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WO2010138915A1 - Implant vestibulaire - Google Patents

Implant vestibulaire Download PDF

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Publication number
WO2010138915A1
WO2010138915A1 PCT/US2010/036729 US2010036729W WO2010138915A1 WO 2010138915 A1 WO2010138915 A1 WO 2010138915A1 US 2010036729 W US2010036729 W US 2010036729W WO 2010138915 A1 WO2010138915 A1 WO 2010138915A1
Authority
WO
WIPO (PCT)
Prior art keywords
electrode
ear
vestibular
electrode contacts
semicircular canal
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/US2010/036729
Other languages
English (en)
Inventor
Steven Bierer
Albert Fuchs
Leo Ling
Kaibao Nie
James Phillips
Jay Rubinstein
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
University of Washington
Original Assignee
University of Washington
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by University of Washington filed Critical University of Washington
Priority to US13/375,196 priority Critical patent/US20120226187A1/en
Publication of WO2010138915A1 publication Critical patent/WO2010138915A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/24—Detecting, measuring or recording bioelectric or biomagnetic signals of the body or parts thereof
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/40—Detecting, measuring or recording for evaluating the nervous system
    • A61B5/4029—Detecting, measuring or recording for evaluating the nervous system for evaluating the peripheral nervous systems
    • A61B5/4041—Evaluating nerves condition
    • A61B5/4047—Evaluating nerves condition afferent nerves, i.e. nerves that relay impulses to the central nervous system
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/74—Details of notification to user or communication with user or patient; User input means
    • A61B5/742—Details of notification to user or communication with user or patient; User input means using visual displays
    • A61B5/743—Displaying an image simultaneously with additional graphical information, e.g. symbols, charts, function plots
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/0526—Head electrodes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/36036—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation of the outer, middle or inner ear
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/3605—Implantable neurostimulators for stimulating central or peripheral nerve system
    • A61N1/36128—Control systems
    • A61N1/36146—Control systems specified by the stimulation parameters
    • A61N1/36167—Timing, e.g. stimulation onset
    • A61N1/36178—Burst or pulse train parameters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/40—Detecting, measuring or recording for evaluating the nervous system
    • A61B5/4005—Detecting, measuring or recording for evaluating the nervous system for evaluating the sensory system
    • A61B5/4023—Evaluating sense of balance
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/72—Signal processing specially adapted for physiological signals or for diagnostic purposes
    • A61B5/7203—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal
    • A61B5/7217—Signal processing specially adapted for physiological signals or for diagnostic purposes for noise prevention, reduction or removal of noise originating from a therapeutic or surgical apparatus, e.g. from a pacemaker
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/02—Details
    • A61N1/04—Electrodes
    • A61N1/05—Electrodes for implantation or insertion into the body, e.g. heart electrode
    • A61N1/0551—Spinal or peripheral nerve electrodes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61N—ELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00—Electrotherapy; Circuits therefor
    • A61N1/18—Applying electric currents by contact electrodes
    • A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372—Arrangements in connection with the implantation of stimulators
    • A61N1/37211—Means for communicating with stimulators
    • A61N1/37235—Aspects of the external programmer
    • A61N1/37247—User interfaces, e.g. input or presentation means

Definitions

  • This invention relates generally to vestibular implant devices and, more specifically, to the installation and use of a vestibular implant device capable of restoring unilateral loss of vestibular function and/or restoring spontaneous type activity to vestibular nerve during Meniere's attacks.
  • Vestibular disorders are very common and often debilitating. People of all ages and backgrounds are affected. Loss or disruption of normal vestibular function results in vertigo, loss of balance and orientation, and falls. Ten percent of patients with vestibular complaints are disabled by their vestibular loss. Vestibular disorders can be idiopathic. Drugs and environmental toxins can adversely affect the inner ear, as can viral infection and a host of genetic disorders.
  • Vestibular disorders can produce paroxysmal attacks of debilitating whirling vertigo and nausea lasting for hours and occurring as frequently as three times a week. While this condition is usually treated medically, at least fifteen percent of patients progress to requiring some sort of surgical intervention including vestibular nerve section, labyrinthectomy, endolymphatic shunt, or intratympanic gentamycin instillation. These procedures put residual hearing at risk to a greater or lesser degree and treatment is typically tailored to the degree of hearing loss in the affected ear. With the exception of the, endolymphatic shunt procedure, which is typically well tolerated but has a significant long- term failure rate, all of these interventions attempt to ablate vestibular function.
  • a vestibular implant is communicatively coupled to a one or more electrode arrays.
  • the electrode arrays are adapted for placement within a semicircular canal of an ear such that the electrode array does not compress the membranous canal.
  • the electrode arrays comprise one or more electrodes.
  • one or more electrodes measure the electrically evoked compound action potentials within a semicircular canal.
  • the measured compound action potentials are sent to a display system, configured to display the measured compound action potentials within a semicircular canal.
  • the disclosed embodiments of the invention provide an apparatus and a method for effectively measuring and displaying compound action potentials within a semicircular canal. Because a high measure of compound action potentials is correlated with a more effective eye movements and consequently higher vestibulo-ocular reflex (VOR), such measurements allow doctors to place an electrode within a semicircular canal at an effective location. For example, if an electrode is placed in a location with low to zero compound action potential, electric stimuli applied to that region will not produce a desired effect of stimulating eye movements. In such cases, a highly invasive surgery would have to be performed again, potentially damaging several functionalities of the ear. Thus, the disclosed embodiments of the invention permit a more precise and effective placement of electrode arrays within a semicircular canal.
  • a vestibular implant is communicatively coupled to an electrode array comprising one or more electrodes.
  • An electrode array is adapted for placement within a semicircular canal of an ear.
  • a stimulator unit housed in a vestibular implant generates electrical stimuli and delivers the stimuli to one or more communicatively coupled electrode arrays. In such an embodiment, the electrodes housed in the electrode array apply the delivered electric stimuli.
  • the stimulator generates an electric pulse train based on a predetermined frequency and amplitude modulation in response to a user input. In another embodiment, the stimulator generates a continuous, unmodulated electric pulse train to deliver to one or more electrode arrays.
  • Vestibular disorders are associated with a loss of afferent activity. For example, the vertigo symptom of Meniere's disease is caused by a loss of spontaneous afferent activity in an ear. Similarly, loss of balance and nausea associated with unilateral vestibulopathy is caused by loss of continuous afferent activity in an ear.
  • the disclosed embodiments of the invention alleviate the symptoms caused by such as loss by providing electric stimuli to certain portions of the semicircular canal.
  • the electric stimulus mimics spontaneous afferent activity, thereby reducing the vertigo of a Meniere's attack.
  • the electric stimuli are continuous and unmodulated, thereby reduce the loss of balance associated with unilateral loss of vestibular function.
  • the disclosed embodiments of the invention provide an apparatus and a method for applying electric stimuli to stop or reduce the vertigo symptoms associated with Meniere's disease and unilateral loss of vestibular function.
  • FIG. 1 is a high-level block diagram illustrating an embodiment of a vestibular implant device.
  • FIG. 2 is a diagram illustrating an embodiment of an external device to control the vestibular implant device.
  • FIG. 3 is an illustration of a graphical user interface to input vestibular stimulation data.
  • FIG. 4 is an illustration of a system to reduce artifacts in recorded electrically- evoked compound action potentials.
  • FIG. 5 is an illustration of an embodiment of a system used to provide stimulation data to a vestibular implant device.
  • FIG. 6 is an illustration of semicircular canals fenestrated near their respective amullae for the insertion of electrode arrays.
  • FIG. 7a is a diagram illustrating an embodiment of an electrode array.
  • FIG. 7b illustrates an embodiment of the trajectory of an electrode array within a semicircular canal once inserted into a canal fenestration.
  • FIG. 1 illustrates an example apparatus 100 to stimulate portions of a vestibular canal according to an embodiment disclosed herein.
  • the apparatus contains a receiver- stimulator 102, which is connectively coupled to electrode arrays 104 and a ball ground electrode 106.
  • the receiver-stimulator 102 comprises a receiving unit 108 and a stimulation unit 110.
  • the receiver- stimulator 102 receives instructions from an external unit 200, described in greater detail below. Responsive to the instructions, the receiver-stimulator 102 outputs a stimulation signal to the electrodes within the electrode arrays 104.
  • the electrodes apply the received electrical stimulation directly to the portion of the semicircular canal in contact with the electrodes.
  • the apparatus 100 may be used to provide electrical stimulation to afferents near the semicircular canal as well as record vestibular electrically-evoked compound action potentials.
  • the receiver-stimulator 102 comprises an internal receiver unit 108 and a stimulator unit 110.
  • the receiver unit 108 receives signals from an external unit 200.
  • FIG. 2 illustrates an example of an external unit 200 according to an embodiment disclosed herein.
  • the external unit 200 comprises an input processing unit 204, a power source 202 and a transmission unit 206.
  • the input processing unit 204 receives instructions regarding an electrical stimulus to send to a receiver-stimulator 102 from an attached computer 208 or another input source.
  • the signal to transmit to a receiver-stimulator 102 is predefined within the input processing unit.
  • the instructions to generate particular electric stimuli may be hard-coded within the input processing unit 204.
  • the input signal received from a computer 208 may instruct the input processing unit 204 to transmit a monopolar or biopolar pulse.
  • the input signal received from a computer 208 is an instruction, instructing the stimulator-receiver unit 102 to generate an electrical stimulus responsive to the instructions.
  • the input processing unit 204 transmits such instructions to the stimulator-receiver unit 102.
  • the input processing unit 204 transmits the signal to the transmission unit 206, to transmit the electric pulse information to the internal receiver unit 108.
  • the external transmission unit 206 comprises an external coil and a magnet secured directly or indirectly to an external coil. The external coils are used to transmit power and stimulation data to the internal receiver-stimulator unit 102.
  • external coil transmits electrical signals (i.e., power and stimulation data) to internal coil via a radio frequency (RF) link, discussed in greater detail below.
  • RF radio frequency
  • a computer connected to the external unit is used to input stimulation data. FIG.
  • FIG. 3 illustrates a graphical user interface for allowing users to deliver arbitrary stimuli to each of electrodes within an electrode array 104 under computer 208 control.
  • a user may user the graphical user interface 300 to control the implant device 100.
  • the computer 208 sends instructions to input processing unit 204.
  • the input processing unit 204 transmits the electric stimulus setting to the receiver unit 108 using a radiofrequency link to the implant.
  • an external device 200 is not used.
  • a pre-programmed processor within the internal device 102 is used to provide stimulation data to the receiver unit 108 or the stimulation unit 110.
  • a signal processor may be used as a stimulator.
  • a signal processing unit 504 uses a SDIO (Secure Digital Input/Output) card 502 to generate the radio frequency (RF) signal carrying stimulation parameters to an external coil 506.
  • RF radio frequency
  • a computer 208 can program the signal processing unit 504 and download the pulse train generation codes to the signal processing unit 504 through a USB connection.
  • the SDIO card 502 has a programmable FPGA for receiving control data and generating RF signals required by a specific communication protocol.
  • signal processing unit 504 can be detached from the PC and servers as a stand-alone processor. Thus, the signal processing unit 504 can process any parameter change request immediately and can be also be potentially used to process rotational signals in real time.
  • signal processing unit 504 stimulator codes can be used or modified to generate a desired pulse train on a specific electrode.
  • a constant-rate and constant-amplitude pulse train may be used. For example, stimulation rate of 200 pps or 600 pps and a pulse width of 400 ⁇ s per phase on a single electrode (monopolar stimulation) may be used.
  • a specific FPGA file for the SDIO card 502 must be generated to produce the desired pulse train. Some unnecessary parts of the signal processing unit 504 stimulator program may need to be removed or changed to bypass the audio processing path in the original program. A new timer to control the package communication between the signal processing unit 504 and the SDIO card 502 may also need to be created. For example, a slider bar can added to the signal processing unit 504 control panel for varying the amplitude of the pulse train from 0 to 255 clinical levels.
  • the internal receiver unit 102 comprises an internal coil, and a magnet fixed relative to the internal coil.
  • the magnets of the receiver unit facilitate the operational alignment of the external and internal coils, enabling internal coil to receive power and stimulation data from external coil.
  • Internal coil is typically a wire antenna coil comprised of multiple turns of electrically insulated single-strand or multi-strand platinum or gold wire. The electrical insulation of internal coil is provided by a flexible silicone molding (not shown).
  • the internal receiver-stimulation unit sends the received power and stimulation data to the communicatively coupled electrode arrays 104.
  • Internal receiver unit and the simulator units are hermetically sealed within a biocompatible housing, shown as the receiver- stimulator unit 102.
  • the electrode arrays 104 have a proximal end connected to the receiver-stimulator unit 102 and a distal end that may be implanted in the semicircular canal of an ear.
  • the receiver-stimulator unit 102 is linked to a trifurcating array 104 of nine electrodes.
  • Different embodiments use electrode arrays and electrode pads of varying sizes, each having varying characteristics and behavior once implanted in the semicircular canal. For example, when compared to a 1.7 mm array with 0.2 mm electrode pads an array of 2.5mm array length and 0.25mm electrode pads provides both device stability and improved impedance.
  • An exemplary embodiment of an electrode array 104 comprising three electrode pads 702 is illustrated in FIG. 7a.
  • the three electrodes 702 within the electrode array 104 are 0.2mm in size. Additional, there is 0.2mm of distance between each electrode pad 702. Finally, FIG. 7a illustrates that the electrode array is 2.5mm in length.
  • the 0.25mm electrode pads 702c have an impedance of approximately 10 kOhm in the operating room after placement within the labyrinth. Three electrode pads are included on each array to permit bipolar or monopolar stimulation as well as recordings of vestibular electrically-evoked compound action potentials. Small movement of the electrode array 104 causes the working array to become ineffective in generating nystagmus (discussed in greater detail below).
  • the length of the electrode array 104 tip is 3.4 mm, allowing for deeper insertion and a more robust and stable electrode array 104.
  • an implanted canal may be activated using monopolar (MP) stimulation of the most proximal electrode of the three-electrode array, and recorded from the most distal electrode in the same canal.
  • MP monopolar
  • separate return electrode may be used for stimulating and recording respectively when both the ball ground electrode and the receiver shell ground are available.
  • the electrodes within the electrode array record electrically- evoked compound action potentials (eCAP) from the semicircular canals where the electrodes are inserted.
  • the electrode measurements are recorded using a recording scope.
  • the recorded compound action potentials measured by an electrode and sent to a display unit configured to display the measured compound action potentials.
  • An evoked compound action potential generally occurs within micro seconds of the stimulation pulse.
  • a vestibular electrode array is driven by a processor and implant receiver.
  • vestibular ECAP recordings are performed by software configured for stimulating one electrode, recording on an adjacent electrode, and then transmitting backward collected neural responses to a control computer.
  • Neural responses usually overlap with the stimulating pulses, resulting in significant stimulation artifacts in ECAP recordings. It is an additional feature of the present apparatus to remove artifacts from the eCAP measurements recorded by one or more electrodes.
  • One method to eliminate the artifact by characterizing the measurement response with the artifact and subtracting the measurement of the artifact alone.
  • a forward masking paradigm is adopted to minimize the artifacts associated with vestibular ECAP recordings. Some parameters were slightly varied across trials.
  • FIG. 4 illustrates the experimental paradigm for artifact reduction in one embodiment of vestibular ECAP recordings.
  • the forward masking paradigm consists of four phases of separate recordings.
  • Phase A a biphasic probe pulse with varying current intensity is presented followed by a brief artifact reduction pulse. After the offset of the probe pulse; the recording window is opened for 1600 microseconds to record any neural activity produced by the probe pulse.
  • Phase B (Masker+Probe): A masker pulse is presented 400 microseconds prior to the probe pulse. The masker pulse could eliminate the response to the probe pulse because the neural elements are in refractory period following presentation of the masker pulse. In this situation, the recording window records only the artifact resulting from the presentation of the probe pulse.
  • Phase C Phase C (Masker only): the same masker pulse is presented to the stimulation electrode.
  • Phase D both, the probe and masker pulses are presented at a minimal level to produce artifacts caused by digital switching.
  • the artifact reduction pulse may be set to 'off to minimize the delay of the recording window, allowing the better capture of the first negative peak.
  • the amplitude of the probe pulse was progressively increased from a sub-threshold level up to the safest level by a step size of 10 clinical levels (CL).
  • an implant can generate a maximum current of 1750 / ⁇ A when x is set to 255.
  • the actual current limit of the implant may be subject to, for example 10V voltage compliance of the current source.
  • the maximum current is around 1000 ⁇ A if the measured electrode impedance is 10 k ⁇ .
  • the electrode impedance of the vestibular prostheses in one embodiment is in the range of 25 k ⁇ to 30 k ⁇ , constraining the maximum current to be less than 400 ⁇ A.
  • the pulse width of each biphasic pulse was set to 50 ⁇ S for both the masker and the probe pulses.
  • the interphasic gap was at 8 ⁇ S. If the artifact reduction pulse was present, it was also set to 50 ⁇ S in pulse width. Recordings were averaged over 50 presentations with a repetition rate of 80 Hz. The amplifier gain was always at 40 dB to avoid saturation.
  • FIG. 6 An electrode may be inserted in the semicircular canal at points 602 indicating an osseous opening for electrode arrays 104.
  • FIG. 7b illustrates that the electrode array 104 is inserted into the semicircular canal fenestration with a trajectory following the curvature of the canal.
  • the subject (or the patient) is prepped and draped in a sterile manner.
  • a post-auricular incision is made with a #15 blade and carried down to the temporalis with a Bovie.
  • a Palva flap is raised exposing the mastoid cortex.
  • a sub-perisosteal pocket is created for the receiver-stimulator 102 posterosuperior to the external auditory canal.
  • a simple mastoidectomy is performed exposing the incus and the target portions of the vestibular labyrinth.
  • Each of the three semicircular canals can then be blue-lined with a lmm diamond burr, fenestrated with an angled pick as illustrated in FIG. 6 and electrodes inserted as shown in FIG.
  • ECAP electrically-evoked compound action potential
  • ECAP recording it can be conducted either when an animal or patient is in sedation during surgery or in awake status post surgery; it is a quick and safe test on whether current stimulation can produce any neural responses at the peripheral level. ECAPs from the auditory nerve have been successfully recorded in animals and in humans with cochlear implants.
  • the morphology of auditory ECAPs provides an objective measure of the excitability of auditory fiber ensemble and it has been clinically proven useful for designing auditory prostheses and predicting subjective threshold for cochlear implant patients.
  • the ECAP recoding is now a standard clinical tool available in most cochlear implant devices through backward telemetry. Stimulation artifact reduction methods, amplitude growth and latency of ECAPs have been extensively studied with cochlear implant patients. Restoring Spontaneous Activity During Meniere's Attacks
  • Meniere's disorder produces recurrent debilitating attacks of vertigo and nausea lasting for several hours. Its cause is believed to be recurring sudden loss of the normal spontaneous activity of the vestibular system in the affected ear. When the spontaneous activity recovers, the vertigo ceases.
  • the disclosed system restores 'spontaneous-like' activity during the attacks through activation of the device described above, thus eliminating the source of the symptoms.
  • An apparatus to restore 'spontaneous-like' activity of vestibular system includes the implant device described above along with a triggering interface between eye -movement recording and vestibular implant activation systems.
  • the stimulation unit 110 is coupled to a user input.
  • a user may input a signal to activate the stimulation unit 110.
  • the stimulation unit 110 Responsive to the user input, the stimulation unit 110 generates electric stimuli to deliver to one or more electrode arrays 104.
  • the electric stimuli may comprise electric pulse trains of varying frequencies and amplitude modulations.
  • the electric stimuli are five short pulse trains on an electrode 104 with an extralyabyrinthine ground electrode 106 with parameters of 200 ⁇ A, 5 pulses, 200 pulses per second, 400 ⁇ s/phase, and 8 ⁇ s interphase gap.
  • other stimuli and combination of stimuli may be provided.
  • the electric characteristics of stimuli to be generated are predetermined based on the effect electric stimuli has on a patient's eye movement and on the Meniere's attack symptoms.
  • eye-movements can be recorded responsive to one or more pulse trains to determine the effect of the pulse train on the eye movement.
  • the appropriate stimulus rate is set on the stimulation unit 110 somewhere between 0 and 300 pps. The effects of level and rate on the resulting eye-movements and any ensuing symptoms are determined.
  • different levels and frequencies of unmodulated pulse trains are mapped to a patient's stimulation unit 110 to allow different levels of vestibular activation to be set.
  • one level may be just below the threshold of eye movements, a second level can be set at the threshold eye movement level and a third level causes large and robust eye movements.
  • These levels of stimulation allow a patient to set the implant device to a level appropriate to the severity of the vertigo attack. Furthermore, an appropriate level of stimulation prevents a level of stimulation so intense that it produces vertigo itself. [0047]
  • the electric stimuli are delivered to one or more electrode arrays 104.
  • the electrode array applies the delivered electric stimuli to the regions of the semicircular canal in contact with electrodes applying the stimuli.
  • Activation of an electrode in the lateral semicircular canal by a biphasic pulse-train burst consistently evokes eye -movements in both vertical and horizontal directions.
  • Experimentation has demonstrated both sustained vertical and horizontal eye movements in response to unmodulated pulse trains, as well as sinusoidal eye-movements in response to sinusoidally frequency-modulated pulse trains. The latter responses showed primarily horizontal eye-movements as desired.
  • the stimulation unit 110 is used to investigate current spread and search for combinations of stimulation parameters that produce the canal-specific eye -movements needed to produce a functional electrically- evoked vestibulo-ocular reflex (eVOR).
  • VOR occurs when the vestibular system works with the visual system to keep objects in focus when the head is moving.
  • an electrode is placed as far from the ampulla as possible so as to minimize potential loss of vestibular function. This increases spread of excitation which could be minimized by placing the electrodes closer to the ampulla. The more focused excitation comes at the cost of greater risk to residual vestibular function, a problem that would not be a concern in treating a patient who already has profound vestibular loss.
  • the vestibular neurostimulation device 100 described above allows electrical activation of the vestibular periphery without further loss of hearing functions.
  • unmodulated 'vestibular pacing' is provided for unilateral vestibulopathy.
  • the stimulator unit 110 provides a steady amplitude electrical pulse to the electrodes 104.
  • the stimulation unit 110 provides stimulation at a level slightly above or below the threshold eCAP levels.
  • unmodulated pacing of the periphery via such a device enhances gain in a diseased labyrinth and suppresses the symptoms associate with unilateral loss of vestibular function.
  • a software module is implemented with a computer program product comprising a computer-readable medium containing computer program code, which can be executed by a computer processor for performing any or all of the steps, operations, or processes described.
  • Embodiments of the invention may also relate to an apparatus for performing the operations herein.
  • Such a computer program may be stored in a tangible computer readable storage medium or any type of media suitable for storing electronic instructions, and coupled to a computer system bus.
  • any computing systems referred to in the specification may include a single processor or may be architectures employing multiple processor designs for increased computing capability.

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Abstract

L'invention concerne un implant vestibulaire qui comporte une unité de stimulation afin de générer des stimuli électriques et de les distribuer à des réseaux d'électrodes. L'unité de stimulation génère des stimuli électriques en réponse à une entrée utilisateur ou bien génère continuellement des stimuli électriques. Les réseaux d'électrodes comportent des électrodes et sont conçus pour être positionnés à l'intérieur d'un conduit auditif semi-circulaire. Les stimuli électriques sont distribués par l'unité de stimulation à l'électrode, de façon que les électrodes appliquent des stimuli électriques. Un stimulus électrique prédéfini est appliqué pour restaurer une activité vestibulaire spontanée au cours d'une attaque de Ménière. Un stimulus électrique continu, non modulé, est appliqué pour supprimer les symptômes de perte unilatérale de la fonction vestibulaire. En outre, les électrodes enregistrent les potentiels d'action composés, évoqués électriquement (eCAP). Un emplacement approprié pour le positionnement du réseau d'électrodes est déterminé en fonction des eCAP enregistrés.
PCT/US2010/036729 2009-05-29 2010-05-28 Implant vestibulaire Ceased WO2010138915A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
US13/375,196 US20120226187A1 (en) 2009-05-29 2010-05-28 Vestibular Implant

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US18253409P 2009-05-29 2009-05-29
US18252609P 2009-05-29 2009-05-29
US61/182,534 2009-05-29
US61/182,526 2009-05-29

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